Systems and methods for adjusting electrical therapy based on impedance changes

TECHNICAL FIELD

The present disclosure is directed generally to systems and methods for adjusting electrical therapy provided to patients, based on changes in the impedance of circuits providing the therapy, including changes detected while applying therapeutic electrical signals to a patient's spinal cord.

BACKGROUND

Neurological stimulators have been developed to treat pain, movement disorders, functional disorders, spasticity, cancer, cardiac disorders, and various other medical conditions. Implantable neurological stimulation systems generally have an implantable pulse generator and one or more leads that deliver electrical pulses to neurological tissue or muscle tissue. For example, several neurological stimulation systems for spinal cord stimulation (SCS) have cylindrical leads that include a lead body with a circular cross-sectional shape and one or more conductive rings spaced apart from each other at the distal end of the lead body. The conductive rings operate as individual electrodes and, in many cases, the SCS leads are implanted percutaneously through a large needle inserted into the epidural space, with or without the assistance of a stylet.

Once implanted, the pulse generator applies electrical pulses to the electrodes, which in turn modify the function of the patient's nervous system, such as by altering the patient's responsiveness to sensory stimuli and/or altering the patient's motor-circuit output. In pain treatment, the pulse generator applies electrical pulses to the electrodes, which in turn can generate sensations that mask or otherwise alter the patient's sensation of pain. For example, in many cases, patients report a tingling or paresthesia that is perceived as more pleasant and/or less uncomfortable than the underlying pain sensation.

One problem associated with existing stimulation systems is that aspects of the systems and/or the interactions between the systems and the patient may change over time. For example, the impedance of a stimulation circuit (which includes implanted electrodes and the patient's tissue) can change as scar tissue forms at the implant site and/or if the lead moves within the patient, and/or if the lead becomes disconnected or undergoes other changes. As the circuit impedance changes, the strength of the applied signal changes, which can reduce the efficacy of the signal and/or create patient discomfort. Accordingly, there remains a need for improved techniques and systems for addressing patient pain in a manner that is effective and comfortable over an extended period of time.

BRIEF DESCRIPTION OF THE DRAWINGS

<figref idrefs="DRAWINGS">FIG. 1A</figref> is a partially schematic illustration of an implantable spinal cord stimulation system positioned at the spine to deliver therapeutic signals in accordance with an embodiment of the present disclosure.

<figref idrefs="DRAWINGS">FIG. 1B</figref> is a partially schematic illustration of a lead having electrode contacts that form elements of one or more therapy circuits having impedances that are detected in accordance with methods of the present disclosure.

<figref idrefs="DRAWINGS">FIG. 2</figref> is a flow diagram illustrating a process for adjusting electrical therapy parameters in response to detected changes in therapeutic circuit impedance.

<figref idrefs="DRAWINGS">FIG. 3</figref> is a flow diagram illustrating further details of processes for detecting and responding to changes in therapy circuit impedance, in accordance with further embodiments of the disclosure.

<figref idrefs="DRAWINGS">FIG. 4A</figref> is a schematic illustration of a representative detection system in accordance with an embodiment of the disclosure.

<figref idrefs="DRAWINGS">FIG. 4B</figref> is a schematic illustration of a representative circuit for detecting impedance changes in accordance with another embodiment of the disclosure.

<figref idrefs="DRAWINGS">FIGS. 5A and 5B</figref> are schematic illustrations of waveforms indicating points at which impedance detection may be performed in accordance with embodiments of the disclosure.

<figref idrefs="DRAWINGS">FIG. 6</figref> is a flow diagram illustrating a process for predicting future values of impedance based on impedance trends in accordance with an embodiment of the disclosure.

DETAILED DESCRIPTION

The present disclosure is directed generally to systems and methods for adjusting electrical therapy parameters based on detected changes in the impedance of an electrical circuit that provides the electrical therapy. Specific details of certain embodiments of the disclosure are described below with reference to adjusting therapy parameters for spinal cord stimulators, which may be used to treat chronic pain. However, the disclosed systems and methods may be used in the context of other stimulators and/or other patient conditions. Accordingly, some embodiments can have configurations, components, or procedures different than those described in this section, and other embodiments may eliminate particular components or procedures. A person of ordinary skill in the relevant art, therefore, will understand that the invention may have other embodiments with additional elements, and/or may have other embodiments without several of the features shown and described below with reference to <figref idrefs="DRAWINGS">FIGS. 1A-6</figref>.

Overview

During the course of a typical spinal cord stimulation therapy regimen and/or a trial period leading up to the therapy regimen, the impedance of the electrical circuit that provides electrical therapy to the patient may change for any variety of reasons. For example, if the patient changes position and the implanted lead carrying the therapy electrodes shifts, the circuit impedance may change because the electrodes are now adjacent to tissue and/or fluid having different impedance characteristics. If the circuit impedance changes suddenly, the patient may experience a sudden change in the applied current and/or voltage, potentially causing patient discomfort. In other cases, scar tissue may be present at implant and/or build up on the electrodes, decreasing the efficacy with which the electrical signals are provided to the patient. In still other cases, individual electrodes may short together, or the lead may become disconnected or partially disconnected from the signal generator, creating one or more open circuits that reduce or eliminate the efficacy of the therapy. In any of these instances, certain aspects of the following disclosure can automatically detect changes in circuit impedance and automatically respond to the changes in a manner that improves patient comfort and/or improves the efficacy of the therapy.

A method in accordance with a particular embodiment of the disclosure includes applying a therapeutic electrical signal to a patient via an implanted portion of a patient stimulation system that includes a signal delivery device in electrical communication with a target neural population of the patient. The electrical signal is delivered in accordance with one or more signal delivery parameters. The method can further include detecting a change in the impedance of an electrical circuit that includes the signal delivery device, using the implanted portion of the patient stimulation system. Based at least in part on the detected impedance change, the method can still further include automatically adjusting the value of the signal delivery parameter(s) without human intervention. Accordingly, the process of detecting impedance changes and responding to the detected changes can be performed autonomously by the implanted portion of the patient stimulation system.

A method in accordance with another aspect of the disclosure includes automatically identifying changes in the impedance of an electrical circuit that provides therapy to the patient, as a function of time. Based at least upon identifying the changes in impedance as a function of time, the method can further include predicting a future value of the impedance and automatically performing a task based on the predicted future value. Representative tasks include predicting a lead failure, confirming that an identified impedance trend conforms with an expected trend, and/or providing notice to a patient or practitioner of a predicted change in impedance value.

Representative Systems and Methods

In the following discussion, <figref idrefs="DRAWINGS">FIGS. 1A-1B</figref> illustrate a representative implementation of a system implanted in the patient's spinal cord region, and <figref idrefs="DRAWINGS">FIGS. 2-6</figref> illustrate representative methods and associated circuits and waveforms for detecting impedance changes and responding to the detected changes. <figref idrefs="DRAWINGS">FIG. 1A</figref> schematically illustrates a representative treatment system <b>100</b> for providing relief from chronic pain and/or other conditions, arranged relative to the general anatomy of a patient's spinal cord <b>191</b>. The system <b>100</b> can include a pulse generator <b>101</b>, which may be implanted subcutaneously within a patient <b>190</b> and coupled to a signal delivery element <b>109</b>. In a representative example, the signal delivery element <b>109</b> includes a lead or lead body <b>110</b> that carries features or elements for delivering therapy to the patient <b>190</b> after implantation. The pulse generator <b>101</b> can be connected directly to the lead body <b>110</b>, or it can be coupled to the lead body <b>110</b> via a communication link <b>102</b> (e.g., an extension). As used herein, the terms lead and lead body include any of a number of suitable substrates and/or support members that carry devices for providing therapy signals to the patient <b>190</b>. For example, the lead body <b>110</b> can include one or more electrodes or electrical contacts that direct electrical signals into the patient's tissue, such as to provide for patient relief. In other embodiments, the signal delivery element <b>109</b> can include devices other than a lead body (e.g., a paddle) that also direct electrical signals and/or other types of signals to the patient <b>190</b>.

The pulse generator <b>101</b> can transmit signals to the signal delivery element <b>109</b> that up-regulate (e.g., stimulate or excite) and/or down-regulate (e.g., block or suppress) target nerves. As used herein, and unless otherwise noted, the terms “stimulate” and “stimulation” refer generally to signals that have either type of effect on the target nerves. The pulse generator <b>101</b> can include a machine-readable (e.g., computer-readable) medium containing instructions for generating and transmitting suitable therapy signals. The pulse generator <b>101</b> and/or other elements of the system <b>100</b> can include one or more processors <b>107</b>, memories <b>108</b> and/or input/output devices. Accordingly, the process of determining impedance and taking follow-up action can be performed by computer-executable instructions contained on computer-readable media, e.g., the processor(s) <b>107</b> and/or memory(s) <b>108</b>. The pulse generator <b>101</b> can include multiple portions, elements, and/or subsystems (e.g., for directing signals in accordance with multiple signal delivery parameters), housed in a single housing, as shown in <figref idrefs="DRAWINGS">FIG. 1A</figref>, or in multiple housings. In any of these embodiments, the pulse generator <b>101</b> and/or other implanted components of the system <b>100</b> can include elements for detecting and responding to impedance changes.

In some embodiments, the pulse generator <b>101</b> can obtain power to generate the therapy signals from an external power source <b>103</b>. The external power source <b>103</b> can transmit power to the implanted pulse generator <b>101</b> using electromagnetic induction (e.g., RF signals). For example, the external power source <b>103</b> can include an external coil <b>104</b> that communicates with a corresponding internal coil (not shown) within the implantable pulse generator <b>101</b>. The external power source <b>103</b> can be portable for ease of use.

In another embodiment, the pulse generator <b>101</b> can obtain the power to generate therapy signals from an internal power source, in addition to or in lieu of the external power source <b>103</b>. For example, the implanted pulse generator <b>101</b> can include a non-rechargeable battery or a rechargeable battery to provide such power. When the internal power source includes a rechargeable battery, the external power source <b>103</b> can be used to recharge the battery. The external power source <b>103</b> can in turn be recharged from a suitable power source (e.g., conventional wall power).

In some cases, an external programmer <b>105</b> (e.g., a trial stimulator) can be coupled to the signal delivery element <b>109</b> during an initial implant procedure, prior to implanting the pulse generator <b>101</b>. For example, a practitioner (e.g., a physician and/or a company representative) can use the external programmer <b>105</b> to vary the stimulation parameters provided to the signal delivery element <b>109</b> in real time, and select optimal or particularly efficacious parameters. During this process, the practitioner can also vary the position of the signal delivery element <b>109</b>. After the position of the signal delivery element <b>109</b> and appropriate signal delivery parameters are established using the external programmer <b>105</b>, the patient <b>190</b> can receive therapy via signals generated by the external programmer <b>105</b>, generally for a limited period of time. In a representative application, the patient <b>190</b> receives such therapy for one week. Assuming the trial therapy is effective or shows the promise of being effective, the practitioner then replaces the external programmer <b>105</b> with the implanted pulse generator <b>101</b>, and programs the pulse generator <b>101</b> with parameters selected based on the experience gained during the trial period. Optionally, the practitioner can also replace the signal delivery element <b>109</b>. Once the implantable pulse generator <b>101</b> has been positioned within the patient <b>190</b>, the signal delivery parameters provided by the pulse generator <b>101</b> can still be updated remotely via a wireless physician's programmer (e.g., a physician's remote) <b>111</b> and/or a wireless patient programmer <b>106</b> (e.g., a patient remote). Generally, the patient <b>190</b> has control over fewer parameters than does the practitioner. For example, the capability of the patient programmer <b>106</b> may be limited to starting and/or stopping the pulse generator <b>101</b>, and/or adjusting stimulation amplitude.

In any of the foregoing embodiments, the parameters in accordance with which the pulse generator <b>101</b> provides signals can be modulated during portions of the therapy regimen. For example, the frequency, amplitude, pulse width, duty cycle, and/or signal delivery location can be modulated in accordance with a preset program, patient and/or physician inputs, and/or in a random or pseudorandom manner. Such parameter variations can be used to address a number of potential clinical situations, including changes in the patient's perception of pain, changes in the preferred target neural population, and/or patient accommodation or habituation. Such parameter changes can also be implemented automatically to account for detected impedance changes.

<figref idrefs="DRAWINGS">FIG. 1B</figref> illustrates a representative lead <b>110</b> that can be connected to the pulse generator <b>101</b>. The lead <b>110</b> can have any suitable number of contacts C positioned along its length L for delivering electrical therapy to the patient. For purposes of illustration, 11 contacts C, identified individually as contacts C<b>1</b>, C<b>2</b> . . . C<b>11</b> are shown in <figref idrefs="DRAWINGS">FIG. 1B</figref>. In operation, one or more of the contacts C is cathodic and another one or more of the contacts C is anodic. The contacts C can be individually addressable so that any contact C or combination of contacts C can operate as a cathode, and any contact C or combination of contacts C can operate as an anode. The contacts C can be electrically grouped in any of a wide variety of combinations, and individual contacts C can perform different functions (e.g., cathodic functions and/or anodic functions) at different times during the course of a therapy regimen. In any of these embodiments, each contact C may be coupled with a corresponding conductor <b>111</b> to the pulse generator <b>101</b>. The conductors <b>111</b> may have one or more connection points along their lengths (e.g., at a junction with the pulse generator <b>101</b>, and optionally at a junction with an extension). Accordingly, the circuit for a given pair of contacts C includes the contacts C, the patient tissue T between the contacts, the individual conductors <b>111</b>, connection points along the conductors <b>111</b>, and connection points between the conductors <b>111</b> and the pulse generator <b>101</b>. As discussed below, aspects of the present disclosure are directed to detecting changes in the overall circuit impedance that may result from changes at any of a variety of points along the circuit, and providing an appropriate response.

<figref idrefs="DRAWINGS">FIG. 2</figref> illustrates an overall process <b>220</b> in accordance with a particular embodiment of the disclosure. The process <b>220</b> includes applying electrical therapy to a patient via an implanted or partially implanted system (process portion <b>225</b>). During the course of the therapy, the process <b>220</b> can further include detecting a change in the impedance of an electrical circuit that provides the therapy, using the implanted portion of the system (process portion <b>226</b>). Based on the detected impedance change, the process <b>220</b> can still further include automatically adjusting signal delivery parameters in accordance with which the therapy is provided, without human intervention (process portion <b>227</b>). The signal delivery parameters can include signal strength, the location and/or number of electrical contacts delivering therapy to the patient, and/or other parameters. <figref idrefs="DRAWINGS">FIG. 3</figref> describes further aspects of particular embodiments of the foregoing process.

<figref idrefs="DRAWINGS">FIG. 3</figref> is a block diagram illustrating in further detail aspects of the overall process <b>220</b> described above with reference to <figref idrefs="DRAWINGS">FIG. 2</figref>. Process portion <b>221</b> includes identifying a target neural population. For example, process portion <b>221</b> can include identifying one or more neural populations at particular vertebral locations along the patient's spine. Process portion <b>222</b> includes implanting an electrical therapy system, for example, implanting the signal delivery element <b>109</b> and the pulse generator <b>101</b> described above with reference to <figref idrefs="DRAWINGS">FIGS. 1A and 1B</figref>. As discussed above with reference to <figref idrefs="DRAWINGS">FIG. 1B</figref>, the electrical therapy system includes at least one electrical therapy circuit which has associated with it an initial impedance value. In process portion <b>225</b>, electrical therapy is applied to the patient via the implanted system with the initial impedance value. The impedance value may change over time, which is detected in process portion <b>226</b>. The electrical therapy signals are typically time-varying signals (e.g., pulses), and the associated circuit can include capacitive and/or resistive elements. Accordingly, the detected impedance can include capacitive and/or resistive components. In particular embodiments, the system can distinguish between resistive and capacitive components of the overall impedance, and use this information to select the appropriate signal delivery parameter to vary. For example, if the impedance change is primarily capacitive, changing the signal delivery frequency may have a greater effect than if the impedance change is primarily resistive.

The change in impedance of the electrical circuit can be detected by detecting a change in power applied to the circuit (process portion <b>227</b>), a change in voltage at one or more points along the circuit (process portion <b>228</b>), a change in current passing through the circuit (process portion <b>229</b>), and/or changes in other values. In a particular embodiment (process portion <b>230</b>), the impedance of the electrical therapy circuit is detected while the therapy signal is delivered, for example, by sampling the therapy signal itself. In other embodiments, a dedicated electrical signal can be applied to the electrical therapy circuit and sampled, so as to detect impedance and/or impedance changes, independent of the therapy signal (process portion <b>231</b>). Accordingly, this arrangement can be used to detect impedance and/or impedance changes of a therapy circuit without the need for the therapy signal to be active on the circuit at that time.

In any of the foregoing embodiments, the process <b>220</b> can include different steps depending upon the magnitude and/or direction of the impedance change. In a particular embodiment, process portion <b>232</b> can include determining whether the impedance change is an increase or a decrease. If the change is an increase, process portion <b>233</b> can include determining whether the circuit is open. An open circuit can be indicated by an infinite impedance, or by an impedance or impedance increase that exceeds a suitable threshold value.

Process portions <b>234</b>-<b>240</b> may be performed if, in process portion <b>233</b>, it is determined that the electrical therapy circuit is open. For example, process portion <b>234</b> can include reducing the signal strength (e.g., the applied current and/or voltage) prior to closing or attempting to close the open circuit (process portion <b>235</b>). In particular embodiments, process portion <b>234</b> can include reducing the signal strength to zero, or to a suitable non-zero value such that when the circuit is later closed, the patient does not receive an uncomfortable sensation. Process portion <b>235</b> can, for example, include changing one or more of the contacts (e.g., those shown in <figref idrefs="DRAWINGS">FIG. 1B</figref>) that form a portion of the electrical therapy circuit. This change can be achieved by opening and closing appropriate switches at the pulse generator <b>101</b>. Once the change has been made, process portion <b>236</b> can include gradually increasing the strength of the signal applied to the therapy circuit. By first reducing the signal strength (process portion <b>234</b>) and then gradually increasing the signal strength after the change in the circuit has been made (process portion <b>236</b>), the process <b>220</b> can avoid subjecting the patient to a sudden increase in the applied signal, which may cause patient discomfort.

Once the signal strength has been increased, process portion <b>237</b> can include checking the impedance to determine whether it has returned to its original level, or has otherwise achieved an acceptable level. This process can include checking the power, voltage, and/or current, as described above with reference to process portions <b>227</b>-<b>229</b>. If the impedance is at an acceptable level, process portion <b>238</b> includes continuing to deliver the therapy. In addition, the patient and/or practitioner can be notified that a change has been made to account for the detected increase in impedance. The notification can take any of a variety of suitable forms, including a vibratory signal, and/or an internally stored signal that is downloaded external to the patient during a battery recharge operation or diagnostic operation. If the change did not result in an adequately improved impedance level, then in process portion <b>239</b>, the system checks to determine whether all the contacts of the implanted lead have been checked. If not, the process returns to process portion <b>234</b> and a different contact is placed in the circuit. If, after all of the contacts have been checked and determined to form an open circuit, this can indicate that the lead is disconnected, which is flagged for the user and/or practitioner in process portion <b>240</b>, using any suitable notification technique. In process portion <b>250</b>, the system checks for lead reconnection, e.g., by rechecking all contacts for an open circuit. Once the lead has been reconnected, the system returns to process portion <b>236</b> so as to gradually increase signal strength.

If in process portions <b>232</b> and <b>233</b>, the system determines that the impedance has decreased, or has increased but not so much as to indicate an open circuit, then in process portion <b>241</b>, the signal delivery parameters are adjusted in an autonomous manner to bring the impedance values to acceptable levels. Process portion <b>241</b> can in turn include changing any of a variety of signal delivery parameters as identified by process portions <b>242</b>-<b>245</b>. For example, process portion <b>242</b> can include changing the number of active contacts in the electrical therapy circuit. The number of active contacts may be increased in particular embodiments if the circuit impedance increases (e.g., to provide parallel electrical paths), and may be decreased in other embodiments if the impedance decreases. In a particular example, the patient may change position or the lead may change position relative to the patient such that the circuit impedance increases because the active contacts are now positioned adjacent to a portion of the patient tissue having a higher impedance. By increasing the number of active contacts, the resulting circuit can include portions of the patient tissue having a lower impedance. Of course, when such a change is made, it is made so that the resulting therapy is still applied to the appropriate portion of the patient tissue, even though the range over which the active contacts are positioned and may now be expanded. For example, only a subset of the contacts shown in <figref idrefs="DRAWINGS">FIG. 1B</figref> may be used and/or available for such a change, so as to avoid directing the therapy signal too far from the originally intended neural population.

In other embodiments, the system can automatically detect a decrease in the impedance of the therapy circuit. For example, if the lead shifts to a location within the patient that results in a lowered impedance, the system can automatically detect this occurrence. One such example is if the lead shifts from an initial position so as to be in closer proximity to cerebral spinal fluid, which has a relatively low impedance. In such instances, the number of electrical contacts applying the therapy may be decreased. In any of the foregoing embodiments once the responsive change has been made, the process can continue with process portion <b>251</b>, which includes determining whether the new circuit produces a target impedance value. If so, then in process portion <b>238</b>, the system delivers additional therapy. In addition, the system can notify the patient and/or practitioner of the update. If the change has not produced a target impedance value, the process returns to process portion <b>241</b>. At that point, process portion <b>242</b> can be re-executed using a different combination of electrodes, or any of process portions <b>243</b>-<b>245</b> can be executed.

Process portion <b>243</b> includes changing the contacts that are active, for example, without increasing or decreasing the number of active contacts. In a particular example, process portion <b>243</b> can include substituting one contact for another. The substituted contact can be an anodic contact or a cathodic contact, and in some embodiments, both anodic and cathodic contacts can be changed. Once the contacts have been changed, the impedance is checked (process portion <b>251</b>) and the process continues in a manner generally similar to that discussed above.

Process portion <b>244</b> includes adjusting the signal strength (increasing or decreasing the strength) in response to an indication that an impedance has changed. The signal strength can correspond to a voltage level, a current level, and/or a power level. Process portion <b>244</b> can in turn include selecting an updated strength value (e.g., an updated voltage value or current value) as shown in process portion <b>252</b>, and then determining whether the updated strength value exceeds a predetermined compliance value (process portion <b>246</b>). For example, a typical constant current source provides signals at a constant current by modulating the applied voltage, but keeping the applied voltage below a predetermined compliance voltage value, e.g., a programmed compliance voltage. If the selected updated strength value does not result in the compliance value being exceeded, then the impedance can optionally be rechecked in process portion <b>251</b> and the system can then deliver additional therapy (process portion <b>238</b>). The impedance check at process portion <b>251</b> may be optional in this case because changing the signal strength may not change impedance.

If, in process portion <b>246</b> it is determined that the compliance value is exceeded by the selected updated strength value, then in process portion <b>247</b>, the compliance value is adjusted. As discussed above, a constant current source automatically adjusts the applied voltage to account for at least some changes in the circuit impedance, so as to effectively produce a constant current. If the circuit impedance increases beyond a level that can be accommodated by a voltage change that remains within the maximum compliance voltage value, the compliance voltage can be adjusted, within preset limits that are established to provide for patient safety and comfort. Accordingly, in process portion <b>248</b>, the system determines whether such a preset limit on the degree to which the compliance voltage can be adjusted has been exceeded. If it has not, then the impedance can optionally be checked (process portion <b>251</b>) and the therapy delivered to the patient (process portion <b>238</b>). If the necessary compliance value exceeds the preset limit, then in process portion <b>249</b>, the user and/or the practitioner can be notified that the recommended signal strength is not available without exceeding preset limits on the amount by which the compliance value can be changed. In addition to or in lieu of providing such notification, the process can automatically revert to one of the other available methods for adjusting the signal delivery parameters, including process portion <b>242</b> (changing the number of active contacts), process portion <b>243</b> (changing which contacts are active), and/or process portion <b>245</b> (changing other parameters). The other parameters that may be changed can include, but are not limited to, frequency, pulse width, and/or duty cycle.

In some embodiments, the compliance voltage value is increased, e.g., to account for an increased circuit impedance. In other embodiments, the compliance voltage value is decreased, e.g., in response to an impedance reduction. In any of the foregoing embodiments, it can be advantageous to keep the compliance value as low as possible, while still providing signals at an effective signal strength, so as to reduce the power consumed by the system. Accordingly, the system can automatically adjust the compliance margin (e.g., the difference between the compliance voltage and actual delivered voltage). For example, the system can automatically set the compliance margin to be a fixed level (in volts or millivolts) above the actual delivered voltage (e.g., the updated strength value). In other embodiments, the compliance margin can be a fixed percentage of the updated strength value. In still further embodiments, the compliance margin can vary, and can be automatically adjusted based on the range of requested strength perturbations, e.g., the degree to which the updated strength values deviate from the strength value being applied at that time. If the range is wide, the compliance margin can be correspondingly wide to avoid having to repeatedly adjust the compliance value. If the range is narrow, the compliance margin can be correspondingly narrow to reduce power consumption. Accordingly, in particular embodiments, the system can automatically track the foregoing perturbations and automatically adjust the compliance margin.

In particular instances, the foregoing arrangement can track the gradual reduction in the range of impedance perturbations that result when a newly implanted lead becomes “scarred in.” The system can also track increases in the range of impedance perturbations if the scar tissue continues to build up in a manner that requires frequent upward adjustments in signal strength, and/or if the lead and/or patient undergo other changes that affect circuit impedance.

The systems and methods described above can operate in accordance with a variety of different modes. For example, during a first mode of operation, the system can check the impedance of one or more circuits that include only active therapy contacts. If, during the first mode of operation, the system identifies an impedance change in association with the active contact(s), it can then check the impedance of inactive contacts during a second mode of operation. Based on the impedance measurements obtained during the second mode, the system can automatically change which contacts are active and which are inactive. This arrangement can reduce the time and power required to perform an impedance check because inactive contacts are checked only when an impedance change is identified in association with one or more active contacts.

One feature of several embodiments described herein is that the system <b>100</b> can automatically identify changes in impedance via an implanted portion of the system, and automatically take appropriate action without patient or practitioner intervention. An advantage of this feature is that the system need not rely on external analysis and/or diagnostics, and accordingly can implement the action more quickly and/or more conveniently.

Another feature of several of the embodiments described herein is that the system <b>100</b> can automatically identify an open circuit (e.g., a disconnected lead) and then gradually increase the strength of the applied therapy signal once the open circuit has been closed. An advantage of this feature is that it can reduce or eliminate the likelihood for the patient to feel a sudden shock or discomfort, which may otherwise result when the therapy signal is suddenly re-applied at the target strength value.

Still another feature of several of the embodiments described herein is that the system <b>100</b> can automatically adjust a preset compliance level (e.g., a voltage or current) to account for impedance changes. While increasing the compliance level may reduce overall system efficiency (e.g., may result in an increased power consumption), the patient can receive dynamically updated and effective therapy in a short period of time. This arrangement can allow the patient to continue receiving effective therapy until the power source is recharged or replaced, as opposed to potentially requiring that the patient undergo an in-office procedure to address the source of the impedance change (e.g., lead movement or scar tissue).

Yet another feature of several of the disclosed embodiments is that the system can detect impedance changes while the patient is receiving therapy. Accordingly, the patient's therapy need not be interrupted to provide this function. In addition, the system can not only check the impedance of the lead contacts applying therapy at a given time, but also other contacts. Accordingly, the system can readily identify alternate contacts that may be substituted for or provided in addition to the currently active contacts, to address changes in impedance. In addition, this arrangement allows the system to rapidly identify conditions that may affect contacts other than just the currently active contacts. Such conditions include a disconnected lead.

<figref idrefs="DRAWINGS">FIG. 4A</figref> is a schematic illustration of portions of the system <b>100</b> used for impedance detection in accordance with an embodiment of the disclosure. The system <b>100</b> can include an impedance detector <b>119</b> that in turn includes a microcontroller or microprocessor <b>107</b> that is coupled to an analog-to-digital (A/D) converter <b>112</b>. The ND converter <b>112</b> is coupled to a stimulation circuit <b>113</b> that includes one or more electrical contacts, and is implanted in the patient <b>190</b>. Accordingly, the A/D converter <b>112</b> converts analog signals (e.g., voltage and/or current levels) to digital values, which are analyzed by the microprocessor <b>107</b> to identify impedance changes.

<figref idrefs="DRAWINGS">FIG. 4B</figref> is a representative circuit diagram of an embodiment of the system <b>100</b> described above with reference to <figref idrefs="DRAWINGS">FIGS. 1 and 4A</figref>. In this particular embodiment, the A/D converter <b>112</b> is connected to a voltage divider <b>114</b>, which is in turn selectively couplable to the stimulation circuit <b>113</b> via an enable measurement switch <b>115</b>. In other embodiments, the voltage divider <b>114</b> can be replaced with other suitable elements, for example, an amplifier. In any of these embodiments, the stimulation circuit <b>113</b> can include a constant current source <b>116</b> that receives a compliance voltage input <b>117</b>, which can in turn be initially preset and then optionally adjusted within further preset limits, as discussed above. The constant current source <b>116</b> can be coupled to a contact selector <b>118</b>, which is in turn connected to the contacts C<b>1</b>, C<b>2</b> . . . C<b>11</b> positioned at the patient <b>190</b>. The contact selector <b>118</b> can include any of a wide variety of suitable switching devices used to select one or more of the contacts C<b>1</b>-C<b>11</b> for applying therapy to the patient, and/or for impedance detection. The circuit can include an H-bridge or other suitable element to selectively reverse the current direction for one or more combinations of contacts C. In other embodiments, the system <b>100</b> can include other suitable arrangements, for example, a constant voltage source rather than a constant current source, a current sink in addition to the constant current source, and/or other suitable arrangements known to those of ordinary skill in the relevant art.

In any of the foregoing embodiments, the detector <b>119</b> will typically detect the impedance of a circuit that includes at least two contact, e.g., C<b>1</b> and C<b>2</b>. If the circuit impedance increases beyond a preset threshold, the system can automatically step through the remaining contacts, e.g., C<b>1</b> in combination with C<b>3</b>, C<b>1</b> in combination with C<b>4</b>, and so on. This sequential process can be completed for any combination of contacts that may be suitable for continuing the patient therapy. In any of these cases, however, the impedance of the tested circuit will include the impedances of all the contacts in the circuit. Accordingly, the microprocessor <b>107</b> can include one or more of a variety of provisions for isolating impedance changes to a particular contact or contacts. For example, in one case, a nominal impedance can be assigned to other contacts included in the circuit (e.g., if multiple contacts are coupled in parallel in the circuit), and then subtracted from a total impedance to obtain the impedance for a given contact. In another embodiment, a series of multivariable equations can be used to solve for the impedance of each individual contact. Such an implementation is expected to consume more power than others, and accordingly, may in at least some embodiments be selected only when suitable power is available. In another approach, the microprocessor <b>107</b> can employ a successive approximation technique by using an initially measured value for one contact to estimate values for other contacts, and then repeating the process as the impedances of circuits with other contacts are identified. In any of the foregoing embodiments, the detector <b>119</b> obtains impedance values and/or changes in impedance values which are provided as inputs to other functional elements of the microprocessor <b>107</b> that automatically implement the changes described above with reference to <figref idrefs="DRAWINGS">FIGS. 2 and 3</figref>.

<figref idrefs="DRAWINGS">FIG. 5A</figref> illustrates a representative waveform <b>570</b><i>a </i>having multiple pulses <b>571</b>, each with a cathodic phase <b>572</b> and an anodic phase <b>573</b> for delivering therapy to the patient. In a particular aspect of this embodiment, the waveform <b>570</b><i>a </i>can be sampled directly (e.g., at the cathodic phase <b>572</b>) via the circuit described above with reference to <figref idrefs="DRAWINGS">FIG. 4B</figref>, to identify circuit impedance. For example, arrow S identifies a suitable sampling point. In particular embodiments, the waveform <b>570</b><i>a </i>can be sampled at multiple points, and the results analyzed to provide a complex impedance value.

<figref idrefs="DRAWINGS">FIG. 5B</figref> illustrates another waveform <b>570</b><i>b </i>having multiple bursts of pulses <b>571</b> separated by a quiescent period. In this embodiment, a separate detection pulse <b>574</b> can be superimposed on the waveform <b>570</b><i>b </i>at the quiescent period. The impedance characteristics of the circuit are accordingly determined by analyzing the impedance associated with the detection pulse <b>574</b>. In still further embodiments, the detection pulse <b>574</b> can be applied to a circuit that is not applying therapy at that time, in which case the waveform <b>570</b><i>b </i>is entirely quiescent except for the presence of the detection pulse <b>574</b>. In any of these embodiments, the detection pulse <b>574</b> is typically provided at subthreshold leads to avoid triggering a motor and/or sensory response in the patient.

In any of the foregoing embodiments, the therapy signal can be applied at frequencies ranging from about 1.5 kHz to about 100 kHz, duty cycles of from about 50% to about 100%, e.g., with the stimulation signal on for a period of about 10 milliseconds to about 2 milliseconds, and off for a period of about 1 millisecond to about 1.5 milliseconds. The applied pulses can have a width of from about 30 to 35 microseconds and an amplitude in the range of about 1 mA to about 4 mA. Other representative parameters are included in co-pending U.S. Provisional Application No. 61/176,868, incorporated herein by reference. In other embodiments, these parameters can have different values suitable for providing patient therapy to any of a variety of neural populations to address any of a variety of patient conditions.

<figref idrefs="DRAWINGS">FIG. 6</figref> is a flow diagram illustrating a process <b>620</b> in accordance with another embodiment of the disclosure. Process <b>620</b> can include applying electrical therapy to the patient (process portion <b>625</b>), and automatically identifying changes in the impedance of an electrical circuit via which the therapy is applied, as a function of time (process portion <b>626</b>). Based on the information obtained in process portion <b>626</b>, process portion <b>627</b> can include predicting a future value of the impedance. For example, the future value can be predicted by a suitable extrapolation technique, including a linear or higher order function, a least-squares curve fit, or other technique. Based on the predicted future value of the impedance, process portion <b>628</b> can include automatically performing a task, e.g., without human intervention. Representative tasks can include predicting a lead failure, e.g., if the lead impedance intermittently becomes excessive. In other embodiments, process portion <b>628</b> can include predicting excessive impedance such as may result from the formation of scar tissue around a lead, for example, if the impedance exhibits a steady growth. Still another function that may be performed via process portion <b>628</b> includes confirming that the impedance trend identified in process portion <b>626</b> conforms with an expected trend, for example, an expected trend or schedule resulting from an expected amount of scar tissue growth. In still another embodiment, the task can include updating any of the signal delivery parameters described above, and/or adjusting the compliance values and/or compliance margins, as discussed above. In any of these embodiments, process portion <b>628</b> can include notifying the patient and/or practitioner, alone or in combination with any of the foregoing activities.

From the foregoing, it will be appreciated that specific embodiments of the disclosure have been described herein for purposes of illustration, but that various modifications may be made without deviating from the disclosure. For example, while certain aspects of the disclosure were described above in the context of spinal cord stimulation to treat chronic pain, similar techniques may be used in other embodiments to identify impedance changes and/or trends for therapy applied to other neural populations and/or for other patient conditions. The signal delivery parameters described above may have other values in other embodiments, for example, lower frequencies than the 1.5 kHz-100 kHz range described above. The detection circuits can have arrangements other than those specifically disclosed herein. The microprocessor can implement responses to the detected impedance changes using any of a variety of suitable programming languages and techniques.

Certain aspects of the foregoing disclosure described in the context of particular embodiments may be combined or eliminated in other embodiments. For example, the process of predicting impedance trends discussed above with reference to <figref idrefs="DRAWINGS">FIG. 6</figref> may be combined with the process for adjusting impedance values described above with reference to <figref idrefs="DRAWINGS">FIGS. 2 and 3</figref>. The impedance values may be tracked in a manner that is coordinated with patient position or activity, as is disclosed in co-pending U.S. Provisional Application No. 61/151,464, incorporated herein by reference. The method of tracking impedance changes as a function of time and predicting future impedance values need not be performed by an implanted portion of the system in some embodiments, and can instead be performed outside the patient. Further, while advantages associated with certain embodiments have been described in the context of those embodiments, other embodiments may also exhibit such advantages, and not all embodiments need necessarily exhibit such advantages to fall within the scope of the present disclosure.